Methods and devices for determining sensing device usability

ABSTRACT

Methods and devices for determining sensing device usability, e.g., for self-monitoring and point of care devices. In one embodiment, the invention is to a method of determining device usability, comprising the steps of providing a device comprising a first electrical pad; a second electrical pad; and a humidity-responsive polymer layer contacting at least a portion of the first and second electrical pads; applying a potential across the first and second electrical pads; measuring an electrical property associated with the humidity-responsive polymer layer; and determining whether the measured electrical property associated with the humidity-responsive polymer layer has exceeded a humidity threshold level associated with the device usability.

CROSS REFERENCE TO RELATED APPLICATIONS

This application is a divisional application of U.S. patent applicationSer. No. 13/537,983, filed Jun. 29, 2012, which claims priority to U.S.Provisional Application No. 61/579,247, filed on Dec. 22, 2011, and toU.S. Provisional Application No. 61/503,234, filed on Jun. 30, 2011, theentireties of which are incorporated herein by reference.

FIELD OF THE INVENTION

The present invention relates to methods for determining deviceusability. In particular, the invention relates to such methodsinvolving the application of a potential across a continuous polymermatrix and measuring an electrical property to determine whether thedevice has exceeded a threshold level associated with device usability.

BACKGROUND OF THE INVENTION

A multitude of self-monitoring and laboratory tests for analytes ofinterest are performed on biological samples for diagnosis, screening,disease staging, forensic analysis, pregnancy testing, and drug testing,among others. While a few qualitative tests, such as glucose,prothrombin and pregnancy tests, have been reduced to simple kits for apatient's home use, the majority of quantitative tests still require theexpertise of trained technicians in a laboratory setting usingsophisticated instruments. Laboratory testing increases the cost ofanalysis and delays the patient's or clinician's receipt of the results.In many circumstances, this delay can be detrimental to the patient'scondition or prognosis, such as for example the analysis of markersindicating myocardial infarction and heart failure. In these and similarcritical situations, it is advantageous to perform such analyses at thepoint-of-care, accurately, inexpensively and with minimal delay.

Self-monitoring tests are generally performed using in-home sampleanalysis systems, e.g., blood glucose monitoring devices. In-homeanalysis systems generally include a reusable reading apparatus thatperforms sample tests using a plurality of disposable devices (e.g.,electrochemical test sensors or test strips) that can be loaded into thereading apparatus. An example of such a system is the PRECISION™ line ofblood glucose and ketone body monitoring systems sold by Abbott DiabetesCare, Inc., Alameda, Calif., USA. Each individual electrochemical testsensor typically includes a substrate that is formed as a thin,rectangular strip of non-conductive material, and a plurality ofcarbon-layer electrodes deposited on the substrate with one electrodefunctioning as the reference electrode and one electrode functioning asthe working electrode for the test sensor. In a reaction area of thesubstrate, an enzyme is deposited on the working electrode, and when thepatient sample is exposed to the enzyme, the analyte, e.g., glucose,undergoes a chemical reaction, which produces a measurable electricalresponse.

Point-of-care sample analysis systems are generally based on a reusablereading apparatus that performs sample tests using a disposable device(e.g., a cartridge or strip) that contains analytical elements (e.g.,electrodes or optics for sensing analytes such as, for example, pH,oxygen, glucose, or ketone body). The disposable device can optionallyinclude fluidic elements (e.g., conduits for receiving and deliveringthe sample to the electrodes or optics), calibrant elements (e.g.,fluids for standardizing the electrodes with a known concentration ofthe analyte), and dyes with known extinction coefficients forstandardizing optics. In operation, the user may select a disposabledevice with the required panel of tests (e.g., electrolytes,metabolites, cardiac markers and the like), draw a sample, dispense itinto the device, optionally seal the device, and insert the device intothe reading apparatus to communicate the data to an LIS/HIS foranalysis. An example of such a system is the i-STAT® system sold byAbbott Point-of-Care, Inc., Princeton, N.J., USA. The i-STAT® portableblood analysis system typically comprises Wi-Fi-enabled readerinstruments that work in conjunction with single-use blood testingcartridges that contain sensors for various analytes. For furtherinformation on the i-STAT® portable blood analysis system, seehttp://www.abbottpointofcare.com/.

Self-monitoring and point-of-care sample testing systems eliminate thetime-consuming need to send a sample to a central laboratory fortesting. For instance, self-monitoring generally requires frequentmeasurements of a concentration of a particular analyte in a body fluide.g., blood, of a patient, and the in-home analysis systems allow thepatient to obtain a reliable qualitative results frequently throughoutthe day. Additionally, point-of-care sample testing systems allow a usere.g. a nurse and physician, at the bedside of a patient, to obtainreliable, quantitative, analytical results, comparable in quality tothat which would be obtained in a laboratory.

Analyzers for self-monitoring and point-of-care testing, such as aself-contained disposable sensing device or cartridge and a reader orinstrument, are further described in U.S. Pat. No. 7,418,285 toGhesquiere et al. and U.S. Pat. No. 5,096,669 to Lauks, et al., theentireties of which are incorporated herein by reference. In generaloperation of the analyzers, a fluid sample to be measured is drawn intoa device and the device is inserted into the reader through a slottedopening. Data generated from measurements performed by the reader may beoutput to a display and/or other output device, such as a printer, or,as described in greater detail below, via a wireless network connection.The disposable device may contain sensing arrays and several cavitiesand conduits that perform sample collection, provide reagents for use inmeasurement and sensor calibration, and transport fluids to and from thesensors. Optionally, reagents may be mixed into the sample for testing.Sensing arrays in the device measure the specific chemical species inthe fluid sample being tested. The electrochemical sensors are exposedto and react with the fluid sample to be measured generating electricalcurrents and potentials indicative of the measurements being performed.The electrochemical sensors may be constructed dry and when thecalibrant fluid flows over the electrochemical sensors, the sensorseasily “wet up” and are operational and stable for calibration andcomposition measurements. These characteristics provide many packagingand storage advantages, including a long shelf life. Each of the sensingarrays may comprise an array of conventional electrical contacts, anarray of electrochemical sensors, and circuitry for connectingindividual sensors to individual contacts. The electrical signals arecommunicated to a reader enabled to perform calculations and to displaydata, such as the concentration of the results of the measurement.

Although the particular order in which the sampling and analytical stepsoccur may vary between different self-monitoring systems, point-of-caresystems, and providers, the objective of providing rapid sample testresults in close proximity to a patient remains. The reading apparatus(e.g., Precision Xtra® Blood Glucose Monitoring System, i-STAT® analyzeror other analyzer) may then perform a test cycle (i.e., all the otheranalytical steps required to perform the tests). Such simplicity givesthe patient or physician quicker insight into the patient'sphysiological status and, by reducing the time for monitoring ordiagnosis, enables a quicker decision by the patient or physician ondisease management or appropriate treatment, thus enhancing thelikelihood of a successful patient treatment.

In the emergency room and other acute-care locations within a hospital,the types of sample tests required for individual patients can varywidely. Thus, point-of-care systems generally offer a range ofdisposable devices configured to perform different sample tests, orcombinations of such tests. For example, for blood analysis devices, inaddition to traditional blood tests, including oxygen, carbon dioxide,pH, potassium, sodium, magnesium, calcium, chloride, phosphate,hematocrit, glucose, urea (e.g., BUN), creatinine and liver enzymes,other tests may include, for example, prothrombin time (PT), activatedclotting time (ACT), activated partial thromboplastin time (APTT),troponin, creatine kinase MB (CKMB), and lactate. Although devicestypically contain between one and ten tests, it will be appreciated bypersons of ordinary skill in the art that any number of tests may becontained in a device.

A given hospital may use numerous different types of test devices andtest instruments at multiple point-of-care testing locations within thehospital. These locations can include, for example, an emergency room(ER), a critical care unit (CCU), a pediatric intensive care unit(PICU), an intensive care unit (ICU), a renal dialysis unit (RDU), anoperating room (OR), a cardiovascular operating room (CVOR), generalwards (GW), and the like. Other non-hospital-based locations wheremedical care is delivered, include, for example, MASH units, nursinghomes, and cruise, commercial, and military ships.

In some cases, test strips and cartridges have a shelf life, which mayvary widely depending on the specific test strip or cartridge as well asupon storage conditions. For example, some cartridges may have a shelflife of about six to about nine months when refrigerated, but a muchmore limited shelf life, e.g., about two weeks at room temperature, or,more specifically, about ten weeks at up to about 30° C. As a result,hospitals typically store cartridges at a central refrigerated location,and deliver cartridges to specific locations as demand requires. Theselocations can include, for example, an emergency room (ER), criticalcare unit (CCU), pediatric intensive care unit (PICU), intensive careunit (ICU), renal dialysis unit (RDU), operating room (OR),cardiovascular operating room (CVOR) and general wards (GW). Theselocations may or may not have available refrigerated storage, and thiswill impact product lifetime and, as a result, the inventory they willhold. Further complicating device management is the fact that a givenuser, such as the patient, may store the test strips in an impropermanner, e.g., at an unsuitable temperature or humidity, or a user, suchas a hospital, may use multiple types of cartridges, each having adifferent shelf life. Alternatively, the user may be a physician'soffice laboratory or visiting nurse service. However, the need to ensurequality remains the same.

U.S. Patent Appl. No. US 2009/0119047 to Zelin et al., the entirety ofwhich is incorporated herein by reference, discloses an improved qualityassurance system and method for point-of-care testing. It providesquality assurance for laboratory quality tests performed by a bloodanalysis system at the point of patient care without the need forrunning liquid-based quality control materials on the analysis system.Quality assurance of a quantitative physiological sample test system isperformed without using a quality control sample by monitoring thethermal and temporal stress of a component used with the test system.Alert information is generated that indicates that the component hasfailed quality assurance when the thermal and temporal stress exceeds apredetermined thermal-temporal stress threshold.

U.S. Pat. No. 7,612,325 to Watkins Jr., et al., the entirety of which isincorporated herein by reference, discloses electrical sensor formonitoring degradation of products from environmental stressors anddescribes an environmental degradation sensor for environmentallysensitive products such as food, pharmaceuticals or cosmetic productsprovides the degraded state and estimated remaining life of the product.The sensor is made of a polymeric matrix and conductive filler. Acontrol agent, selected to adjust a reaction rate of the sensor toenvironmental conditions, allows correlation of an electrical propertyof the sensor to a degraded state of the product.

Application Note 2004-2, “A Comparison of Relative Humidity SensingTechnologies,” Hygrometrix Inc., 2004, the entirety of which isincorporated herein by reference, discloses that the transduction ofwater vapor concentration into an electrical measurement by a sensingfilm comprises three processes: (i) physical and chemical interaction ofwater vapor molecules with the film surface; (ii) surface and bulkmodifications of the film due to water vapor accumulation on anddiffusion into the film; and (iii) electrical measurement of a keyelectrical or mechanical property of the film that changes due to itsinteraction with water vapor. The sensing films are typically made ofpolyelectrolyte, polymers, and porous ceramic.

In general, the principles of operation for existing types oftime/temperature and time/humidity indicators can be categorized asphysical, chemical and electrical. Examples of physical and chemicalmethods include color change of polymeric materials, chemical reactionsof two elements, physical masking of a marker, melting of a temperaturesensitive material and the like.

However, the use of many existing indicators adds significant cost andcomplexity to the devices they are intended to monitor. This is aparticularly apparent issue for single-use blood testing cartridges andelectrochemical strip devices, e.g., glucose blood testing strips usedby diabetics. Consequently, the need remains for improved low costtime-temperature or time-humidity indicators that are amenable to directintegration into a device manufacturing work flow.

SUMMARY OF THE INVENTION

In one embodiment, the invention is to a method of determining deviceusability, comprising the steps of: providing a device comprising afirst electrical pad; a second electrical pad; and a humidity-responsivepolymer layer contacting at least a portion of the first and secondelectrical pads; applying a potential across the first and secondelectrical pads; measuring an electrical property, e.g., current,resistance, impedance, conductivity, or a combination thereof,associated with the humidity-responsive polymer layer; and determiningwhether the measured electrical property associated with thehumidity-responsive polymer layer has exceeded a humidity thresholdlevel associated with the device usability. Optionally, the methodfurther comprises a step of measuring an initial current valueassociated with the humidity-responsive polymer layer when the device ismanufactured and wherein the humidity threshold level is at least fivetimes lower than the initial current value. As an alternative, themethod may include a step of measuring an initial impedance valueassociated with the humidity-responsive polymer layer when the device ismanufactured, wherein the humidity threshold level is at least fivetimes greater than the initial impedance.

In one aspect, the potential comprises a sigmoidal potential cycle, afixed applied potential, a sequence of fixed applied potential steps, ora combination thereof. The potential optionally comprises a potentialcycle that is applied at a predetermined frequency in the range of about1 Hz to about 100 Hz. The method optionally includes a step of insertingthe device into an analyzer configured to determine whether the measuredelectrical property associated with the humidity-responsive polymerlayer has exceeded the threshold level associated with the deviceusability.

In another embodiment, the invention is to a device having a usabilitythreshold, comprising a first electrical pad, a second electrical pad,and a humidity-responsive polymer layer contacting at least a portion ofthe first and second electrical pads, wherein the humidity-responsivepolymer layer has an electrical property associated with the deviceusability threshold.

In preferred embodiments, the polymer layer is selected from the groupconsisting of a crosslinked polyvinylpyrrolidone (PVP), a crosslinkedpolymer comprising nitrogen-containing heterocyclic groups described in,for example, U.S. Pat. No. 6,932,894, the disclosure of which isincorporated by reference in its entirety, as well as combinationsthereof.

The configuration and shape of the polymer layer may vary widely, but inone embodiment, the continuous polymer layer is substantially circular,preferably domed, and has a diameter of from about 20 μm to about 5 mm.The device may further comprise a boundary structure for controlling thespreading of a dispensed polymer layer precursor to a predeterminedregion of the device, e.g., a ring intersecting said first and secondcontact pads. The first and second pads optionally are separated by adistance of from about 10 μm to about 4 mm.

The device may comprise a sensor selected from the group consisting of apH sensor, oxygen sensor, carbon dioxide sensor, hematocrit sensor,glucose sensor, ketone body sensor, lactate sensor, creatinine sensor,sodium sensor, potassium sensor, magnesium sensor, calcium sensor,chloride sensor, phosphate sensor, liver enzyme sensor, BNP sensor,troponin sensor, BUN sensor, CKMB sensor, NGAL sensor, TSH sensor,D-dimer sensor, PSA sensor, PTH sensor, cholesterol sensor, ALT sensor,AST sensor, prothrombin sensor, APTT sensor, ACT sensor, galectinsensor, and combinations thereof.

In another embodiment, the invention is to a method of correcting asignal generated by an analyte sensor, comprising the steps of providinga device comprising a first electrical pad, a second electrical pad, anda humidity-responsive polymer layer contacting at least a portion ofsaid first and said second electrical pads; applying a potential acrosssaid first and said second electrical pads; measuring an electricalproperty associated with said humidity-responsive polymer layer;determining a correction factor associated with said measured electricalproperty; and applying said correction factor to said signal generatedby said analyte sensor to produce a corrected signal.

In another embodiment, the invention is to a glucose test stripcomprising an integrated humidity detector, said glucose test stripincluding a glucose sensing electrode connected by a first conductiveline to a first electrical contact pad; a reference electrode connectedby a second conductive line to a second electrical contact pad; and apolymer layer that is responsive to humidity, which contacts at least aportion of said first and said second conductive lines.

In another embodiment, the invention is to a method of determiningexposure of a glucose test strip to humidity, the method comprisinginserting said glucose test strip into a glucose meter, said glucosetest strip comprising a glucose sensing electrode connected by a firstconductive line to a first electrical contact pad and a referenceelectrode connected by a second conductive line to a second electricalcontact pad, wherein a polymer layer responsive to humidity positionedon said glucose test strip contacts at least a portion of said first andsaid second conductive lines; applying a potential across said polymerlayer; measuring an electrical property associated with said polymerlayer; and calculating a humidity exposure value from said electricalproperty.

In another embodiment, the invention is to a test strip comprising anintegrated humidity detector for testing one or more analytes, said teststrip including a strip with an analyte sensing electrode connected by afirst conductive line to a first contact pad and a reference electrodeconnected by a second conductive line to a second contact pad; and apolymer layer responsive to humidity positioned on said test strip,which contacts at least a portion of said first and said secondconductive lines, wherein said polymer layer has an electrical propertyassociated with a usability threshold of said test strip.

In another embodiment, the invention is to a handheld electronic devicecomprising a strip port for receiving a test strip, wherein said teststrip comprises a substantially planar strip including an analytesensing electrode connected by a first conductive line to a firstcontact pad and a reference electrode connected by a second conductiveline to a second contact pad; and a polymer layer responsive to humiditypositioned on said test strip, which contacts at least a portion of saidfirst and said second conductive lines, wherein said polymer layer hasan electrical property associated with a usability threshold of saidtest strip; and a processor configured to determine whether saidelectrical property associated with said polymer layer has exceeded saidusability threshold of said test strip.

In another embodiment, the invention is to an analyte testing systemcomprising a test strip comprising a substantially planar stripincluding an analyte sensing electrode connected by a first conductiveline to a first contact pad and a reference electrode connected by asecond conductive line to a second contact pad; and a polymer layerresponsive to humidity positioned on said test strip, which contacts atleast a portion of said first and said second conductive lines, whereinsaid polymer layer has an electrical property associated with ausability threshold of said test strip; and a handheld electronic devicecomprising a strip port for receiving said test strip, and a processor.

BRIEF DESCRIPTION OF THE DRAWINGS

The present invention will be better understood in view of the appendednon-limiting figures, in which:

FIGS. 1a, 1b, and 1c present images showing test strips and partsthereof;

FIG. 2 presents an image showing a connector for a test strip and partsthereof;

FIGS. 3a, 3b, and 3c show side and plane views of a time-humidityindicator (THI) device in accordance with one embodiment of theinvention;

FIGS. 4a and 4b show side and plane views, respectively, of a THI devicewith a boundary structure in accordance with another embodiment of theinvention; and

FIG. 5 presents an image showing a THI device deposited on first andsecond electrical pads in accordance with aspects of the invention.

DETAILED DESCRIPTION OF THE INVENTION

The present invention is best understood in the context of the currentprior art on point-of-care blood analysis and self-monitoring systems.For example, the shelf life of an i-STAT® cartridge (see the i-STAT®system made by Abbott Point of Care, Princeton, N.J., USA) or aFreeStyle Lite® blood glucose test strips (see the FreeStyle Lite®system made by Abbott Diabetes Care Inc., Alameda, Calif., USA) istypically indicated by an expiration date on the product packaging.Specifically, with respect to the i-STAT® cartridge, a refrigerationexpiration date and a room temperature shelf life are provided on theproduct packaging, e.g., on a fluid-containing pouch thereof. Therefrigeration expiration date defines the length of time that thecartridge may be stored under refrigerated conditions after manufacture,e.g., at about 5° C. Depending on the specific device, the refrigerationexpiration date may be about three months, about six months, about ninemonths or about one year after the date of manufacture. The roomtemperature shelf life defines the length of time that the cartridge maybe stored under room temperature (ambient, e.g., 25° C.) conditionsafter a cartridge or a box of cartridges is removed from refrigerationconditions, i.e., removed from a refrigerator. The room temperatureshelf life should not be allowed to exceed the refrigeration expirationdate. The room temperature shelf life is typically on the order of fromtwo to nine weeks, depending on cartridge type. In practice, the roomtemperature expiration date is calculated from the room temperatureshelf life and is written on the box by the user at the time of removalfrom the fridge. Thus, when a box of cartridges is taken out of therefrigerator, the user typically counts the number of days or months todetermine the room temperature expiration date, verifies that the roomtemperature expiration date does not exceed the refrigeration expirationdate printed on the box or cartridge, and writes the room temperatureexpiration date down on the box. Furthermore, when a cartridge is to beused, the end user again checks the expiry dates. This process lendsitself to potential user error in either or both calculating therefrigeration expiration date and/or verifying that the refrigerationexpiration date has not been passed. The present invention is intendedto determine the suitability of the cartridge or test strip for use,i.e., the non-expiration of the shelf life, automatically taking intoconsideration the age of the device as well as the environment, e.g.,temperature and/or humidity, under which the device has been stored.Thus, the user is relieved of this task and the opportunity for auser-induced error is diminished.

While there are several time-temperature, time-humidity, or shelf lifeindicators that are known in the art, it is highly desirable to keep thecost and complexity of the device to a minimum. In the present inventionthis is achieved by providing (or modifying) a pair of electricalcontact pads. Many analytical systems employ electrical orelectrochemical principles and will already have such electrical contactpads as part of the device. Consequently, their use adds no cost as theyare present and necessary for other functions, e.g., are used in analytedetection or in device calibration. The electrical contact pads aredesirably modified so that they can act as shelf life indicators whilestill fulfilling their intended purpose, typically analyte detection ordevice calibration. Thus, the function of the shelf life indicator ofthe invention should also be conducted without diminishing the abilityor performance of the contact pads for their primary purpose, e.g.,signal transmission in analyte sensing or device calibration. It is alsocontemplated, however, that the electrical contact pads that are usedfor time/temperature or time/humidity indication according to someembodiments may be separately provided specifically for performing therole of a shelf life indicator, and do not provide any other role, e.g.,in analyte sensing or device calibration. In this latter aspect,separate contact pads optionally may be provided for analyte detectionand/or device calibration.

The present invention was in part stimulated by the observation that theelectrical resistance of some prototype ion sensor membranes was foundto change after being subjected to elevated humidity conditions forcertain periods of time. The present invention is thus based on thechanging electrical properties, e.g., current flow, resistance and thelike, of a polymer layer or the like that is positioned between andpreferably contacts two adjacent contact pads.

In the present specification, the material that is positioned betweenthe two adjacent contact pads is referred to as a “THI material.” TheTHI material is preferably responsive to the integral of varyinghumidity exposure, and optionally temperature exposure, over time suchthat this gives rise to a predictable change in an electrical propertyof the THI material. For example, in accordance with some aspects of theinvention, a THI relationship between humidity exposure and change inelectrical property may be established such that the electrical propertye.g., conductivity or resistance, of the THI material depends upon anamount of water vapor accumulation on and diffusion into the THImaterial, e.g., the electrical property of the THI material changes dueto its interaction with water vapor.

Devices suitable for use in the present invention include, but are notlimited to, point-of-care and self-monitoring devices such as thosedisclosed in U.S. Pat. Nos. 7,723,099 and 7,802,467, the entireties ofwhich are incorporated herein by reference. In one embodiment, thedevice comprises a first electrical pad and a second electrical pad incontact with a sensor. As used herein, the term “electrical pad” refersto a location wherein electricity may be applied to the device. Theelectrical pads of the present invention may, for example, comprise ametal contact comprising gold, silver, a combination thereof or anothermetal. Suitable sensors for use with the present invention include, butare not limited to, electrochemical sensors, amperometric sensors,potentiometric sensors and conductimetric sensors. Alternatively,neither of the electrical pads are associated with a sensor. Forexample, the device may have a sensor that is independent of theelectrical pads.

The present invention will be specifically described in the context of aglucose test strip, e.g., a FreeStyle Lite® blood glucose test strip,that employs at least two adjacent electrode pads 10 and 20 (e.g., asensing electrode, a reference electrode, a working electrode, and/or acounter electrode), as shown in FIGS. 1a, 1b, and 1c . However, theinvention is not limited to use with blood glucose strips and one ofordinary skill in the art would understand that the present inventioncould be used with many other devices, e.g., an i-STAT cartridge thatemploys at least two adjacent electrode pads, e.g., hematocrit (Hct)electrode pads, or a Hct pad adjacent to an amperometric sensor pad.

In accordance with some aspects of the invention, each electrode pad (orbar) terminates in an electrical contact 30, which is used to makecontact with the connector 40 in a FreeStyle Lite® blood glucose reader,as shown in FIGS. 1a, 1c, and 1d . Features of the connectors aredescribed in US Pat. Pub. No. 2011/0184264, the entirety of which isincorporated herein by reference. As indicated above, the primaryfunctions of integrity checking and blood glucose measurement should notbe affected by the additional use of the electrode pads as part of ashelf life indicator.

In a first embodiment, the present invention relates to a method fordetermining device usability with a time/humidity indicator (THI). Inone embodiment, the method comprises the steps of providing a devicecomprising a first electrical pad, a second electrical pad, and a THImaterial (preferably a continuous humidity-responsive polymer layer)contacting at least a portion of the first and second electrical pads;applying a potential across the first and second electrical pads;measuring an electrical property associated with the THI material; anddetermining whether the measured electrical property associated with theTHI material has exceeded a threshold level associated with the deviceusability.

In one aspect, as shown in FIGS. 3a and 3b , a THI device 100 fordetermining device usability comprises a polymer layer 105 formed inelectrical contact with contact pads 110 and 120. The contact pads 110and 120 may further be in contact with a substrate or base 130(optionally a sensor). As shown, the contact pads 110 and 120 maycomprise terminal portions 140 and 150 of contact lines 160 and 170. Inanother embodiment, not shown, the polymer layer is in electricalcontact with non-terminal portions 180 and 190 of contact lines 160 and170. Thus, the polymer layer (THI material) may be disposed between andin electrical contact with two electrical pads, which may comprise apair of contact pads, a pair of non-terminal contact lines, or acombination thereof.

As shown in FIGS. 3a and 3b , the THI material 200 may be formed bydepositing a THI material precursor 200′ between the two contact pads110 and 120. The THI material 200 may comprise a polymer layer,preferably a continuous polymer layer, and the THI material precursor200′ may comprise a polymer layer precursor. For example, the THImaterial 200 may be formed by depositing, e.g., printing, the THImaterial precursor 200′, e.g., polymer layer precursor, between andpreferably overlapping at least respective portions of the two contactpads 110 and 120, e.g., a working electrode and a counter electrode.

The THI material precursor 200′ may then optionally be treated, e.g.,with heat or other radiation, or dried to form the THI material 200,e.g., continuous polymer layer, in a region between the two contact pads110 and 120, and preferably overlapping at least respective portions ofthe contact pads 110 and 120. This configuration enables the readerinstrument to measure an electrical property of the THI material 200before any sample or calibrant fluid contacts the contact pads 110 and120, which are located in a fluid conduit within the test strip. See,for example, jointly owned U.S. Pat. Nos. 7,802,467 and 7,866,026, theentireties of which are incorporated herein by reference.

In some embodiments, the THI material 200 may comprise a continuoushumidity-responsive polymer layer that includes a polymer matrix. In oneembodiment, the polymer matrix is a crosslinked polymer comprisingnitrogen-containing heterocyclic groups (such as those described in, forexample, U.S. Pat. No. 6,932,894, incorporated herein by reference inits entirety). As an example, the polymer matrix may comprise acrosslinked polyvinylpyrrolidone (PVP), optionally of the type shown inFormula I, below, wherein m ranges from 1 to 4 mol % or is about 2.8 mol%, and n ranges from 96 to 99 mol % or is about 97.2 mol %.

In another embodiment, the polymer matrix comprises a crosslinkedpolymer comprising nitrogen-containing heterocyclic groups of the typeshown in Formula II below. In Formula (II), m optionally ranges from 10to 30 mol % or about 20 mol %, n optionally ranges from 65 to 85 mol %or about 76 mol %, o optionally ranges from 0.5 to 3 mol % or about 1.2mol %, and p optionally ranges from 1 to 5 mol % or about 2.5 mol %.Polymers crosslinked with poly(ethylene glycol) type crosslinkers arepreferred, optionally poly(ethylene glyclol)(400)diglycidyl ether(PEG400).

In another embodiment, the polymer matrix comprises a crosslinkedpolymer comprising nitrogen-containing heterocyclic groups, wherein thecrosslinker comprises triglycidyl glycerol. An exemplary polymer of thistype is shown in Formula III below, wherein o ranges from 5 to 15 mol %or is about 10 mol %, p ranges from 65 to 75 mol % or is about 69 mol %,y ranges from 5 to 15 mol % or is about 10 mol %, z ranges from 0.1 to 1mol % or is about 0.6 mol %, and m ranges from 5 to 15 mol % or is about10 mol %.

In another embodiment, the THI material comprises apolyurethane-acrylate based film, such as those described in Bosch etal., “Polyurethane-acrylate based films as humidity sensors,” Polymer 46at 12200-12209 (2005), incorporated herein by reference in its entirety.

The specific composition of the THI material precursor 200′, e.g.,polymer layer precursor, that is used to form the THI material, e.g.,continuous humidity-responsive polymer layer, may vary widely. In anexemplary embodiment, the THI material precursor 200′ may comprise thepolymer matrix, as discussed above, but preferably further comprises acarrier medium (e.g., solvent) for imparting the desired physicalproperties for deposition thereof as well as solubilizing the polymercontained therein. In another embodiment, the precursor comprises amonomer and an initiator, and polymerization may occur after depositionof the THI material precursor 200′ onto the surface, e.g., through freeradical polymerization, optionally with application of UV radiation.

The carrier medium may comprise water or an organic solvent. As thesematerials are preferably microdispensed onto the contact pads usingmicrodispensing methods and equipment as described in jointly owned U.S.Pat. No. 5,554,339 previously incorporated herein by reference, similarconsiderations as to ingredients, viscosity, surface preparation andpretreatment and the like also apply to the present invention.

The present invention advantageously avoids the need to add conductiveparticles to the THI material, e.g., carbon black, conductive carbonnanotubes, metallic particles, metallic oxide, semi-conductor particles,to adjust the initial resistivity to the desired level. By contrast, thepresent invention, in some aspects, relies on a THI material comprisinga polymer, i.e., a non-conductive material, and hydronium and hydroxylions derived from atmospheric moisture (humidity). While hydronium andhydroxyl ions may be polar or ionic and thus affect the conductivity ofthe THI material, they are not particulate in nature. Nevertheless, inother aspects of the invention, such conductive particles may beincluded in the THI material precursor as well as the THI material usedin the devices and methods of the invention.

As illustrated in FIGS. 3a and 3b , as time increases from the date ofmanufacture of the device 100 and/or as humidity increases, water vaporfrom the atmosphere may diffuse into the THI material 200 such that theconductivity of the THI material 200 increases over time and/or ashumidity increases due to the dissociation of the water molecules intohydronium and hydroxyl ions within the THI material 200. In someembodiments, a potential or potential cycle 210 may be used to take aninitial measurement at the date of manufacture, which may indicate ahigh initial impedance value that would decrease as water vapor diffusesinto the THI material 200 resulting in an increase in conductivity ofthe THI material 200.

In a preferred embodiment, the step of depositing, e.g., printing, theTHI material precursor between the two pads may be accomplished by usinga microdispensing process such as the one described in jointly ownedU.S. Pat. No. 5,554,339, the entirety of which is incorporated herein byreference. This process involves preparing a fluid composition suitablefor forming the polymer layer and loading it into a microsyringeassembly. The microsyringe assembly may comprise, for example, areservoir, a microsyringe needle, a pump for delivering the THI materialprecursor from the reservoir to the microsyringe needle, and amultidirectional controller so that droplets may be brought into contactwith the area between the pads. Automatic alignment of the needle tip tothe dispensing location may be achieved in manufacturing, for example,using an optical recognition system using one or more fiduciary marks.

In a preferred embodiment, particularly for low-cost compatiblemanufacturing methods, the process of depositing the THI materialprecursor may be substantially similar to the printing process that isemployed for the manufacture of sensing membranes onto electrodes (see,e.g., U.S. Pat. No. 5,554,339) and the printing of reagents ontosurfaces or conduit walls of cartridge components for subsequentdissolution into a blood sample.

As described herein, the continuous polymer layer is preferably formedby microdispensing one or more drops of the precursor onto the surfaceand removing the carrier medium, optionally with heat, and/or drying theprecursor to form the THI material. In some embodiments, the depositedprecursor forms a substantially circular shape having a diameter in therange of from about 20 μm to about 5 mm, preferably from 100 μm to about500 μm, and is generally domed, covering the distance between the twopads, which preferably is in the range of from about 10 μm to about 4mm, preferably from about 10 μm to about 200 μm. The average thicknessof the layer is generally in the range of from about 1 μm to about 200μm, preferably from about 20 μm to about 60 μm. One skilled in the artwill appreciate that shapes and ranges outside of those provided abovemay be employed, for example, for larger sensor devices such as somehome use glucose testing strips the precursor may be deposited to form asubstantially rectangular shape that has sides of length from about 20μm to about 5 mm.

The THI material 200 preferably is accurately positioned in the devicein order, for example, to avoid potential contamination of theconnector, e.g., connector pins, in the instrument. Notably, thetransfer of polymeric material from the THI material 200 to theconnector pins should be minimized or avoided. Consequently, in someaspects, the present invention also relates to devices having a boundarystructure 300, as shown in FIGS. 4a and 4b , that facilitatescontrolling the spreading of the dispensed precursor 200′ that forms theTHI material 200, e.g., continuous humidity-responsive polymer layer.The boundary structure 300 may, for example, be positioned at apredetermined region of the device 100, for example as a polygon, e.g.,square, pentagon, hexagon, octagon, and the like, or as a cylindrical orring shape. This boundary structure 300, if employed, preferably ispositioned in a manner that intersects the two adjacent pads 130 and140.

The boundary structure 300 may be formed, for example, by patterning aridge of passivation material, e.g., a photoformable passivationmaterial, such as a photoformable polyimide. The photoformablepassivation material may be spin-coated and patterned to form aninsulating layer over the contact lines on the chip. Thus, the mask forthat process may also include the ring structures. Jointly owned U.S.Pat. No. 5,200,051, the entirety of which is incorporated by reference,discloses similar processes and photoformable materials. Otherphotoformable materials, e.g., those based on polyvinyl alcohol ordichromated gelatin, may also be used.

In the above-described embodiments, connector pin tips may initiallycontact a top portion of the contact pads and move slightly towards themiddle of the chip as the connector applies more force, it is preferredthat the boundary structure 300, e.g., ring, be used for THI material200 positions that are closer to the middle of the chip in order toproperly locate the polymer layer. In this manner, the THI materialpreferably is positioned beyond the extent of travel of the pin tip,thus obviating the contamination issue. For example, the scratch marks410 in the middle of the contact pads 420 and 430 in FIG. 5, show wherethe connector pins have hit the contact pads and moved during connectorengagement in relationship to boundary structure 440.

In accordance with some aspects of the invention, the electricalproperty of the THI material that is measured may be the open circuitresistance (R_(THI)). If the electrical property, e.g., R_(THI)measurement, does not exceed a predetermined threshold value or iswithin a certain range, the device, e.g., test strip, may be consideredvalid for use. For such test strips, depending on how an analyzer isprogrammed, the analyzer may indicate that the test strip has expired orotherwise reject the test strip and abort the test cycle, or engage inanother remedial action, e.g., sensor output correction. Nevertheless,it should be understood, however, that such devices may still besuitable for use but may not have the desired degree of clinicalprecision.

While the present invention is conceived in the first embodiment as aprocess for determining device usability, in a second embodiment, theinvention may be used for sensor correction. Thus, in the firstembodiment, for example, the invention is to a device configured fordetermining device usability comprising a THI material, e.g., acontinuous humidity-responsive polymer layer, formed on a substantiallyplanar surface wherein the surface comprises two adjacent electricalcontact pads. As indicated above, the THI material preferably covers atleast a portion of the two electrical contact pads and a portion of thespace on the surface between the contact pads. In a preferredembodiment, a preselected potential or potential cycle is applied to thepads and the impedance (Z) or current (I) associated with the THImaterial is measured, and the resulting measured value is compared witha predetermined threshold value to determine whether the device isusable.

In the second embodiment, the invention is to a device, a sensor, and aTHI material, e.g., continuous humidity-responsive polymer layer, formedon a substantially planar surface wherein the surface comprises twoadjacent electrical contact pads. The THI material covers at least aportion of the two electrical contact pads and a portion of the space onthe surface between the contact pads. In operation, a preselectedpotential or potential cycle is applied to the contact pads and anelectrical property, e.g., impedance or current, associated with the THImaterial is measured. The measured value is converted to a correctionparameter that is applied to a signal from the output of the sensor toprovide a corrected sensor signal.

In a related embodiment, the invention is to a method of correcting asignal in a sensing device, comprising the steps of: (a) providing asensing device comprising a sensor, a first electrical pad, a secondelectrical pad, and a THI material, e.g., continuous humidity-responsivepolymer layer, contacting at least a portion of the first and secondelectrical pads; (b) applying a potential across the first and secondelectrical pads; (c) measuring an electrical property associated withthe THI material; (d) determining a correction factor associated withthe measured electrical property, e.g., from a look up table or thelike; and (e) applying the correction factor to a signal generated bythe sensor to produce a corrected signal.

In order to determine the appropriate correction factor, e.g., from alook up table or correction algorithm, it is necessary to establish arelationship between the electrical property and the correction factors.Thus, in another embodiment, the invention is to a method of determininga correction factor comprising the steps of: (a) providing a pluralityof devices, each of said devices comprising a sensor; a first electricalpad; a second electrical pad; and a continuous humidity-responsivepolymer layer contacting at least a portion of the first and secondelectrical pads, wherein said devices have been exposed to differentenvironmental conditions; (b) measuring an electrical property of thecontinuous polymer layer for each of the devices; (c) measuring a sensorsignal for a control fluid for each of the devices; and (d) correlatingthe measured electrical properties with the measured sensor signals forthe plurality of devices to determine the correction factor.

In a more generalized embodiment, the invention is to a device having aTHI material, e.g., continuous humidity-responsive polymer layer, formedon a substantially planar surface, wherein the surface comprises twoadjacent electrical contact pads. The THI material covers at least aportion of the two electrical contact pads and a portion of the space onsaid surface between said pads. When a preselected potential orpotential cycle is applied to the contact pads and an electricalproperty, e.g., impedance or current, associated with the THI materialis measured, the measured value determines whether the device is usableand, if the device is usable, whether it is necessary to correct thesignal. If it is necessary to correct the signal, the device maydetermine the appropriate correction factor and modify a sensor signalfrom the device based on the correction factor to provide a correctedsignal. For example a portion of a manufacturing lot of devices can betested under different storage condition and tested with a standardliquid of known composition (control fluid). If the THI value andcontrol fluid values are recorded, any variation between the expectedand measured control fluid value can be correlated with the THI valueand a correction algorithm created. This can then be implemented in theinstrument when running real samples with that manufacturing lot ofdevices.

Various potential cycles may be used in measuring the electricalproperty associated with the THI material. In some exemplaryembodiments, the potential cycle may be selected from a sigmoidalpotential cycle, a fixed applied potential, and a potential that is asequence of fixed applied potential steps. Measurements may be made, forexample, with an impedance measuring circuit in an instrument, or acurrent measuring circuit in an instrument. In a preferred embodiment,an initial current value associated with the THI layer is measured whenthe device is manufactured and the threshold level is at least threetimes, preferably at least five times, lower than the initial currentvalue. Conversely, in another aspect, an initial impedance valueassociated with the THI material is measured when the device ismanufactured and the threshold level is at least three times greater,preferably at least five times greater, than the initial impedance. Insome exemplary embodiments where current is measured, the current rangesfrom picoamps to milliamps, but more typically from nanoamps tomicroamps, e.g., from 0.1 to 100 nanoamps. Where impedance is measure,the typical impedance may range, for example, from below the megaohmrange to above the gigaohm range, more typically in the tens of megaohmsto low gigaohm range, optionally from 100 to 1500 megaohms at afrequency of from about 1 to about 10 Hz.

In embodiments where a sensor correction is made, the correction valuemay be selected from an amperometric correction value, a potentiometriccorrection value, a coulombic correction value and a conductivitycorrection value. These values are typically applied to a sensorselected from the group consisting of a pH sensor, oxygen sensor, carbondioxide sensor, hematocrit sensor, glucose sensor, lactate sensor,creatinine sensor, sodium sensor, potassium sensor, magnesium sensor,calcium sensor, chloride sensor, phosphate sensor, liver enzyme sensor,BNP sensor, troponin sensor, BUN sensor, CKMB sensor, NGAL sensor, TSHsensor, D-dimer sensor, PSA sensor, PTH sensor, cholesterol sensor, ALTsensor, AST sensor, prothrombin sensor, APTT sensor, ACT sensor,galectin sensor, and combinations thereof.

The present invention may be easily adaptable to widely availablecommercial technologies and can be performed with existing electronicsthat require no hardware changes but only a software modification, whichare generally simpler to implement than hardware modifications. Forexample, an i-STAT instrument may be able to measure conductivity at 10kHz and 50 kHz, but may be conveniently expanded to a wider frequencyrange. In a preferred embodiment, this circuitry is programmed tomeasure the electrical resistance between adjacent contact pads at afrequency of 10 Hz. It has been found that low frequency impedancemeasurements in the range of from about 1 Hz to about 100000 Hz are mostsensitive in detecting a change in the electrical property of the THImaterial.

Without being bound by theory, it is understood that changes in circuitimpedance may be due to a change in the bulk membrane resistance, whichis best observed when the ions in the membrane migrate some distance sothey must be under a polarizing voltage for some time, which requires alow frequency. For example, water vapor may be adsorbed into the polymerlayer and dissociated into hydronium and hydroxyl ions that decrease thebulk resistivity and accordingly increase conductivity of the polymerlayer, which can be measured in terms of impedance or conductivity. Onepossible mechanism is that at higher frequencies, the voltage oscillatesso quickly that the ions do not migrate appreciably. As a result, theresistance to their movement does not influence the impedance. Anotherpossibility is that the impedance change over time that is observed inthe present invention may be contributed in part by the electrodeoxidation and its interface with the bulk polymer membrane. In general,electrode polarization impedance becomes more significant at lowerfrequencies than at higher frequencies. In any event, an importantparameter to the present invention is an empirically observable andconsistently predictable change in the electrical property.

To avoid compromising the use of the contact pads for their primaryfunction, typically analyte sensing, where the electrical property thatis measured is the open circuit resistance, the R_(THI) preferably ismuch greater than, e.g., at least 1000 times greater than, the closedcircuit resistance, i.e., the resistance measured between the electrodesattached to the contact pads with either sample or calibrant fluidcovering the electrodes. However, the R_(THI) preferably is much lower,e.g., at least 100 times lower, than the existing open circuitresistance, i.e., the resistance between the contact pins prior tocontacting the pads. This goal may be accomplished through carefuldesign of the geometry of the THI material and control of the THIcomposition. Thus, a reduced cross-sectional polymer layer area and anextended polymer pathlength between the pads will generally lead to anincreased resistance for any given material composition, whereasincreasing the ionic content and ion mobility of the polymer layer for agiven geometry will generally lead to a decreased resistance. Note thatthe typical sample or calibrant fluid resistance is in the range ofabout ten to thousands of ohms, whereas the open circuit resistance isgenerally greater than several giga-ohms. Thus, the THI resistance ispreferably in the mega-ohm to low giga-ohm range.

In one embodiment, a quantitative relationship between R_(THI) andactual aging of a test strip may be established. As indicated herein,the objective is to prevent expired cartridges or test strips from beingused and prevent usable cartridges or test strips from being discarded.Thus, in another embodiment, the invention is to a method of determininga threshold level associated with analytical device usability. Themethod comprises the steps of: (a) providing a plurality of devices,each of said devices comprising a sensor; a first electrical pad; asecond electrical pad; and a continuous humidity-responsive polymerlayer contacting at least a portion of the first and second electricalpads, wherein said devices have been exposed to different environmentalconditions; (b) measuring an electrical property of the continuouspolymer layer for each of the devices; (c) measuring a sensor signal fora control fluid for each of the devices; (d) identifying a subset ofsaid plurality of devices that provide a signal having a predeterminedacceptable precision level for said control fluid; and (e) determiningthe threshold level that corresponds to the electrical property of thecontinuous humidity-responsive polymer layer for the subset of saidplurality of devices.

In accordance with some embodiments of the invention, the invention hasthe advantage that it enables a sensor that would otherwise have beenconsidered to have exceeded its shelf life to still be used based on atime/temperature or time/humidity integrated correction factor. Forexample, once the THI relationship between water vapor (e.g., humidity)exposure and change in impedance has been established, a dynamiccorrection algorithm can be created and embedded into the instrumentsoftware.

An approach to correcting an assay result for aging may rely upon thefollowing. The assay and THI need to predictably change when subjectedto the same thermal or water vapor stress independent of the conditionsto which it has been subjected. For example, an assay storage conditionwith highly fluctuating temperature or humidity (bounded by theallowable extremes) should produce nearly the same change as is observedwhen the assay is stored at a fixed temperature or humidity. If thiscondition is met, and if the time and mean kinetic temperature (MKT) ormean relative humidity (MRH), which is the equivalent fixed temperatureor humidity at which an assay would need to be held to reach the samedegree of aging, are known then the assay result can be corrected. Ifthe duration of thermal or humidity stress is known (ideally the timesince the date of manufacture), the THI can be used to calculate the MKTor MRH. Based upon the relationship established between the MKT or MRHand the change in the assay result, the expected change can be backcalculated from the result. The correction algorithm may be derivedusing an Arrhenius model. For example, a correction factor for glucosemay be determined by the following formula:[Gluc]=b*response−c

-   -   wherein:    -   “response” is the slope of the sensor response (e.g., current)        for the sample;    -   (b) is a calibration parameter for slope (b) of the sensor        response;    -   (c) is a calibration parameter for intercept (c).

With aging, the response slope b is changing according to Arrheniusmodel and glucose concentration can be corrected as follows:

$\lbrack{Gluc}\rbrack = {{\frac{b}{{\theta_{1} \cdot {\exp( {{- ( {\theta_{2} \cdot {\exp( {{- \frac{{Ea}_{Gluc}}{R}} \cdot ( {\frac{1}{M\; R\; H} - \frac{1}{H_{ref}}} )} )}} )} \cdot {time}} )}} + \theta_{3}} \times {Response}} + c}$

wherein:

MRH is the mean relative humidity and can be estimated from the measuredTHI impedance R_(THI);

Ea_(Gluc) is apparent activation energy for change in glucose sensorresponse;

R is the universal gas constant;

H_(ref) is the experimental reference humidity;

θ₁ is a pre-exponential factor for time/humidity changes in b;

θ₂ is the rate of change in b at H_(ref); and

θ₃ is non-humidity dependent offset=1−θ₁.

Advantageously, by utilizing the present invention, it is possible tosignificantly further extend the time available for typical room storageof blood testing devices. In this context, the improvement can be atleast about 50%. In addition, the invention may be applied to anyelectrochemical test device where the instrumentation enables current orimpedance measurements, e.g., glucose meters used for diabetesmonitoring with electrochemical sensor strips. The invention alsosimplifies the process of implementing point of care testing technologyfor the user, e.g., nurse, doctor or other healthcare professional. Italso ensures that test devices, e.g., cartridges, strips and the like,have been stored properly prior to the use of each individual device. Itcan be used to compensate for device aging factors and improve theaccuracy of results throughout the life of the device.

In another embodiment of the present invention, the measured value fromthe THI is used to calculate the remaining percentage of thermal orwater vapor stress for the rest of a manufacturing lot of the samedevices stored under the same conditions. This is essentially the lengthof time for room storage that remains for all of the other devices thatwere stored with the tested device but have yet to be used. As all ofthe devices in a given lot (e.g., a given FreeStyle Lite® blood glucosetest strip manufacturing lot or a given i-STAT cartridge manufacturinglot) are manufactured in the same way and at the same time, the testeddevice gives a measured impedance or current value that not only isrelevant to that particular device (as applied in other disclosedembodiments) but can also be used predictively with respect to otherdevices from the same manufactured lot that have been subjected to thesame storage conditions as the tested device.

For example, assuming a water vapor stress budget of 100% at the timethe lot of test strips are manufactured, at the time a particular teststrip is tested, it is possible to calculate from the measured THI valuethat some fraction of the budget remains, i.e., a value from 100% to 0%(expiry). This is based on an embedded data curve reflecting this rangethat is part of the instrument software algorithm. The curve is derivedfrom data, i.e., factory determined and uploaded to the instrument forpredetermined lots.

Optionally, this information is displayed on the instrument and relayedto the hospital's point of care coordinator. This enables a new supplyof devices, e.g., a new box of cartridges or test strips, to be orderedwhen expiry is imminent. It also enables the creation of a cartridge ortest strip management report that allows the point of care coordinatorto easily monitor and manage cartridges or test strips throughout afacility in a remote manner. Note that in practice, individualcartridges or test strips are generally traceable to a particular boxand it is a reasonable assumption that cartridges or test strips arestored together in the box. Consequently, every time a cartridge or teststrip is run from a particular box it provides useable information onthe amount of room storage for the remaining cartridges or test stripsin that box and all boxes stored similarly.

While the invention has been described in terms of various preferredembodiments, those skilled in the art will recognize that variousmodifications, substitutions, omissions and changes can be made withoutdeparting from the spirit of the present invention. Accordingly, it isintended that the scope of the present invention be limited solely bythe scope of the following claims.

What is claimed is:
 1. A method of determining exposure of a glucosetest strip to humidity, the method comprising: inserting said glucosetest strip into a glucose meter, said glucose test strip comprising aglucose sensing electrode connected by a first conductive line to afirst electrical contact pad and a reference electrode connected by asecond conductive line to a second electrical contact pad, wherein apolymer layer responsive to humidity positioned on said glucose teststrip contacts at least a portion of said first and said secondconductive lines; applying a potential across said polymer layer;measuring an electrical property associated with said polymer layer; andcalculating a humidity exposure value from said electrical property,wherein said polymer layer is selected from the group consisting of acrosslinked polyvinylpyrrolidone (PVP), a crosslinked polymer containingnitrogen heterocyclic groups, and combinations thereof.
 2. The method ofclaim 1, wherein said applying said potential across said polymer layeroccurs prior to applying a blood sample to said glucose test strip. 3.The method of claim 1, wherein said humidity exposure value isassociated with a usability threshold of said glucose test strip.
 4. Themethod of claim 1, wherein said polymer layer comprises hydronium andhydroxyl ions derived from atmospheric moisture.
 5. The method of claim1, wherein the electrical property is an open circuit resistance.
 6. Themethod of claim 5, wherein the humidity exposure value is a meanrelative humidity.
 7. The method of claim 6, further comprisingcorrecting a glucose test result using the open circuit resistance andthe mean relative humidity.
 8. A method of determining exposure of aglucose test strip to humidity, the method comprising: inserting saidglucose test strip into a glucose meter, said glucose test stripcomprising a glucose sensing electrode connected by a first conductiveline to a first electrical contact pad and a reference electrodeconnected by a second conductive line to a second electrical contactpad, wherein a polymer layer responsive to humidity positioned on saidglucose test strip contacts at least a portion of said first and saidsecond conductive lines; applying a potential across said polymer layer;measuring an open circuit resistance associated with said polymer layer;calculating a mean relative humidity from said open circuit resistance;and correcting a glucose test result using the open circuit resistanceand the mean relative humidity.
 9. The method of claim 8, wherein saidapplying said potential across said polymer layer occurs prior toapplying a blood sample to said glucose test strip.
 10. The method ofclaim 8, wherein said mean relative humidity is associated with ausability threshold of said glucose test strip.
 11. The method of claim8, wherein said polymer layer comprises hydronium and hydroxyl ionsderived from atmospheric moisture.